|Publication number||US7878988 B2|
|Application number||US 11/544,248|
|Publication date||Feb 1, 2011|
|Filing date||Oct 6, 2006|
|Priority date||Oct 6, 2006|
|Also published as||US20080161729|
|Publication number||11544248, 544248, US 7878988 B2, US 7878988B2, US-B2-7878988, US7878988 B2, US7878988B2|
|Inventors||Stephen Thomas Bush, Stephen Francis Bush|
|Original Assignee||Stephen Thomas Bush, Stephen Francis Bush|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (15), Non-Patent Citations (12), Classifications (13), Legal Events (1)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This invention relates to biomedical implants and, more importantly, to a system for monitoring the strength of a healing, bone, joint, or ligament union while an orthopedic fixation device such as a plate, pin, or screw is in place.
Bone fractures heal in progressive, complex, sequential steps at the cellular level. The healing process produces osteoid, the precursor of new bone, which eventually undergoes calcification and new bone formation. As healing progresses, the strength of the healing area increases. This same process occurs when physicians operatively stabilize a bone fracture by implanting a bone fixation device such as a plate, pin, or screw. Physicians use similar bone fixation devices after resecting diseased bone and tissue. Another option is to substitute a portion of cadaver bone for the resected bone using an implanted bone fixation device to stabilize the bone junction until healing occurs.
Bone healing takes months for completion, depending on many variables, some of which are unknown and uncontrollable. During the healing process, the repaired area is subject to injury by excessive load applied to the area; yet, studies show that some load to the area promotes healing. Currently, physicians most often monitor bone healing by observing the increase in tissue density and calcification in a series of x-rays. X-rays are subjectively interpreted, frequently inconclusive, and tell little about the strength of the healing repair. Similar limitations apply to special imaging studies such as dual energy x-ray absorptiometry and peripheral quantitative computed tomography. Therefore, physicians must depend on clinical judgment and personal experience when advising patients on safe levels of activity, including movement and weight bearing, involving the repaired site.
Physicians need an objective measure of the degree of healing and strength of the union stabilized by the bone fixation device. Only then may physicians confidently advise patients on what level of effort by the patient the repair can safely bear. Equally important, physicians will avoid needlessly restricting patient activity because the safe level of activity is unknown, hoping to avoid injury to the repaired area. Detailed information on strength of healing not now available would significantly improve patient care and quality of life. Improvements in the cost of medical care would be significant but are beyond the scope of this patent application.
Several methods to measure bone strain received U.S. patents. The device of Yen, et al. described in U.S. Pat. No. 5,456,724 (1995) appears useful during surgery to install bone grafts but is not implantable for strain measurements during healing. The device of Orsak, et al. described in U.S. Pat. No. 5,695,496 (1997) measures light transmission through an optical fiber attached to an external bone fixation apparatus. This method is not applicable to commonly used implanted bone fixation procedures.
The system of Elvin, et al. described in U.S. Pat. No. 6,034,296 (2000) utilizes an implantable bone strain sensing system mounted on or in the bone fixation hardware. Some components must be hermetically sealed and mounted by adhesives to the bone fixation device. Eliminating the need for adhesives and seals and making the sensor system an integral part of the bone fixation device would improve reliability of operation. Vigorous manipulation sometimes necessary during surgical installation of the bone fixation device subjects all parts mounted on the bone fixation hardware to risk of damage during surgery. Also the added mass of foreign material introduced in the body comprising the mounted sensing system adds to the risk of complications during surgery and later recovery. Variations in the physical properties, such as density, of the attached materials comprising the sensing system compared to the properties of the bone fixation device increase the risk of implant failure. An ideal sensing system would be an integral part of the bone fixation device with no measurable increase in mass of foreign materials introduced into the body or variation in physical properties from the fixation device.
Morgan, et al. in U.S. Pat. App. No. 20060052782 described a monitoring system employing one or more sensors and microchips attached to a bone-fixation device. These attachments are subject to failure of adhesion to the fixation device, failure of seals protecting the components, and the danger of damage during surgical installation of the fixation device. Pressure and strain measurements from the discreet focus of the sensing site may not apply to the implant as a unit. Focal changes such as swelling or shrinkage of tissue during normal healing may confound readings intended to reflect forces on the entire fixation device. Sensor readings depend on radio frequency transmission, which is subject to interference and distortion in many environments. The ideal monitoring system would provide direct readings of strain on the fixation device as a single, bone-stabilizing unit with a sensing system integral to the fixation device.
The physical properties and electrical conduction characteristics of carbon nanotubes make them well suited to provide the basis for measuring the strength of healing of bone repairs. Since carbon nanotubes are molecular structures, they do not add any significant foreign mass to a bone fixation device. Carbon nanotubes may even add strength to a bone fixation device.
The diameter of a nanotube is on the order of a few nanometers (approximately 50,000 times smaller than the width of a human hair), while they can be up to several millimeters in length thus exhibiting a very high aspect ratio, referring to the ratio of length to width. The tubes occur naturally in random orientations and can be imbedded in or on various materials. Changes in tube length and/or orientation by even a micron or less alter the effective electrical resistance of the nanotube network. This alteration in electrical resistance is measured by current flow and indicates the stress and strain on the implant. Stress is the application of force per unit area on the implant; strain is the ratio of extension in length when loaded, to the original length of the implant.
Accordingly, the objects and advantages of the present invention are:
Further objects and advantages will be apparent after considering the ensuing description and drawings.
The present invention comprises a method to measure the strength of healing bone, joint, or ligament repairs when an orthopedic fixation device is used to stabilize the defective area.
DRAWINGS -- REFERENCE NUMERALS
Proximal healthy bone segment
Distal bone segment
Healing area between bone segments
Bone fixation plate
Power source connector
Electric current source
Bone fixation plate 14 is implanted using a plurality of anchors such as attachment screw 15, as usually performed by surgeons skilled in the art. The bone healing process begins promptly, as described above. When the physician wishes to monitor the strength of healing area between bone segments 12, testing cuff 16 is placed around the extremity encompassing the site of healing area between bone segments 12. Connections are made to power source 17 and to analyzer 18. When power source 17 is activated, electric current pulses through active coil 16 a, causing an induced electric current to flow in bone fixation plate 14. The induced electric current in bone fixation plate 14 produces a corresponding secondary induced current in passive coil 16 b. Analyzer 18 measures the secondary induced current.
A reading from analyzer 18 is made while patient is at rest. A series of additional readings is made with increasing loads placed on healing area between bone segments 12. If loads increase to the point that analyzer 18 indicates strain on bone fixation plate 14, testing ceases. Analyzer 18 detects strain on bone fixation plate 14 by indicating a decrease in the secondary induced current in passive coil 16 b compared to the resting state reading. This decrease in the secondary induced current results from the reduction in current flow through bone fixation plate 14, a property of its carbon nanotube component in response to strain from the applied load. The indication of strain shows that healing has not occurred sufficient to bear the load applied. The physician will then advise patient to engage only in activities producing a lesser load on bone fixation plate 14. Active patients would greatly appreciate knowing this limit. Additionally, the physician can encourage patient to engage in activities at a level that is safe as determined by the load applied prior to evidence of strain on bone fixation plate 14.
As healing area between bone segments 12 becomes stronger, the greater the load it can bear without causing strain on bone fixation plate 14. Bone healing may be considered complete when the maximum load supported by healing area between bone segments 12 is equal to the load that can be borne by the corresponding opposite side of the patient's body. Alternatively, healing may be considered complete when the maximum load not causing strain on bone fixation plate 14 approximates the load bearing capacity by similar, closely matched individuals. Such studies on normal individuals are commonly performed in medical research. At this point, physicians will know that the bone fixation device may be removed, if medically desirable.
Implanted bone fixation devices are subject to failure from breaking. This method will detect early evidence of loss of integrity of a bone fixation device. Any disruption of the carbon nanotube component of bone fixation plate 14 by even a partial break will cause an increase in electrical resistance at rest compared to past readings by analyzer 18. Similarly a loosened attachment screw 15, also having a component of carbon nanotubes, will cause an increase in electrical resistance to current flow in bone fixation plate 14. Prompt medical intervention and surgical revision of the repair will prevent extensive injury from an unexpected break of bone fixation plate 14.
Bone fixation devices other than plates include rods, screws, nails, wires, clamps, prostheses, and others, any of which may incorporate carbon nanotubes or other high-aspect ratio, electrical conducting nano-particles, allow this method to measure the strength of healing.
Carbon nanotubes may be incorporated into resins such as polymethylmethacrylate described by Pienkowski, et al. in U.S. Pat. No. 6,872,403 (2005). Such resins may be used to stabilize repaired areas, allowing this invention to measure the strength of healing.
Some materials other than carbon form nanotubes that exhibit the electric current conduction properties in response to strain. These other materials may substitute for carbon and this invention will measure strength of healing.
The preferred embodiment emphasizes physicians and patients, but veterinary applications are obvious. Because test results are based on objective measurements of electric current changes through the bone fixation device, no response is required from the test subject.
Analyzer 18 may display the test result and sound an alarm when a load indicates strain on the bone fixation device. This will prevent injury from overloading the repaired area during testing.
Analyzer 18 may transmit test results to other external devices by direct or wireless communication permitting remote monitoring.
This method of measuring strength of healing may be used on patients not aware of pain due to treatment, medication, or illness. Pain sometimes provides a signal that a safe load limit has been reached or exceeded, but pain is unreliable for preventing further injury from overloading. Conversely, excessive fear of pain or fear of further injury may inhibit the patient from performing actions that are safe and beneficial to healing. This method for measuring strength of healing adds important information that will give confidence and encouragement to proper use of the repaired area during healing.
This method permits continuous monitoring for strain on bone fixation plate 14 by wearing testing cuff 16 while performing predetermined actions. An alarm on analyzer 18 can be made to sound when activity unexpectedly causes strain on the bone fixation device. Thus, advising patients on permissible activities and warning against excessively strenuous activities are based on objective, real-time test results.
This method is readily adaptable to external bone fixation devices. A carbon nanotube component incorporated in the rigid external bone fixation device permits testing for strain on the device with load bearing by direct contacts to an electric current source and to analyzer 18.
Similarly, direct measurement of electric current changes caused by strain as described for this method may be performed when bone fixation devices are implanted in sites where a detection cuff is not usable or the bone fixation device is very short. Electric leads attached to the ends of the bone fixation device may be brought to skin surface 13 where direct contact can be made for appropriate studies as described above. To reduce infection risk contact leads may remain below the skin surface where electrical contact can be made using sterile needles during testing. This is similar to the principle of implanting vascular access devices beneath the skin to minimize infection risk for patients receiving chemotherapy or renal dialysis.
When bone, ligament, or joint repairs require use of bone adhesives, the adhesives may be compounded to include carbon nanotubes as described by Pienkowski, et al. in U.S. Pat. No. 6,872,403 (2005). This method can then measure the strength of healing bone, ligament, joint, and related tissues.
This invention will measure bone strength in areas at high risk for fracture, such as brittle bones, by using limited surgery to attach a carbon nanotube-containing rigid rod to the bone in order to measure the limit of load capacity. This will allow the patient to know the safe level of activity similar to repaired bone areas.
It is feasible to inject carbon nanotube containing materials to stabilize weak areas of bones and ligaments. The present invention can be used to measure safe loads for these treated areas.
The present invention permits non-invasive measurement of strength of healing at the site of bone repair by using rigid materials incorporating carbon nanotubes to stabilize the repair. This device can, with some modification, provide a means to measure bone healing in any area of the body. The present method will assess healing of joints or ligaments that have been repaired by rigid materials similar to bone fractures or resections. This device is safe since only graduated loads on the repaired area are used, thus minimizing risk of injury during testing. This device provides objective information not available by any method to measure healing of bone and related structures. The measurements by this device are important to patients who require guidance on limiting activities that may cause injury, as well as encouragement to engage in safe activities with confidence that injury will not occur. Thus, debilitating muscle atrophy from prolonged disuse during healing can be minimized. This invention provides real-time display of results on a continuous or episodic basis using appropriate alarm warnings when injurious loads are approached.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2231702 *||Feb 25, 1939||Feb 11, 1941||Westinghouse Electric & Mfg Co||Strain gauge|
|US4576158 *||Jan 10, 1984||Mar 18, 1986||Region Wallone||Method for determining the stability of an orthopedic device composed of an external fixation bar during setting of bone fractures|
|US4646754 *||Feb 19, 1985||Mar 3, 1987||Seale Joseph B||Non-invasive determination of mechanical characteristics in the body|
|US4920806 *||Feb 16, 1989||May 1, 1990||Kabushiki Kaisha Toshiba||Strain gage|
|US5456724||Dec 15, 1993||Oct 10, 1995||Industrial Technology Research Institute||Load sensor for bone graft|
|US5695496||Jan 17, 1995||Dec 9, 1997||Smith & Nephew Inc.||Method of measuring bone strain to detect fracture consolidation|
|US6034296||Dec 4, 1997||Mar 7, 2000||Elvin; Niell||Implantable bone strain telemetry sensing system and method|
|US6755831 *||Nov 30, 2001||Jun 29, 2004||Regents Of The University Of Minnesota||Wrist surgery devices and techniques|
|US6809462 *||Dec 6, 2001||Oct 26, 2004||Sri International||Electroactive polymer sensors|
|US6848320 *||May 29, 2003||Feb 1, 2005||Matsushita Electric Works, Ltd.||Mechanical deformation amount sensor|
|US6872403||Jan 31, 2001||Mar 29, 2005||University Of Kentucky Research Foundation||Polymethylmethacrylate augmented with carbon nanotubes|
|US20020049394 *||Aug 24, 2001||Apr 25, 2002||The Cleveland Clinic Foundation||Apparatus and method for assessing loads on adjacent bones|
|US20020166382 *||Oct 20, 2001||Nov 14, 2002||Bachas Leonidas G.||Magnetoelastic sensor for characterizing properties of thin-film/coatings|
|US20050107870 *||Aug 20, 2004||May 19, 2005||Xingwu Wang||Medical device with multiple coating layers|
|US20060052782||Jun 7, 2005||Mar 9, 2006||Chad Morgan||Orthopaedic implant with sensors|
|1||Asai, H, et al., Noninvasive evaluation of bone stiffness by combining microdefocusing method and reflectance method, Proceedings of the 1998 IEEE Ultrasonic Symposium, vol. 2, pp. 1459-1462, 1998.|
|2||Ashe, MC, Accuracy of pQCT for evaluating the aged human radius: an ashing, histomorphometry and failure load investigation, Osteoporosis International, vol. 17, pp. 1241-1251, 2006.|
|3||Balasundaram, G, et al., Nanomaterials for osteoporosis treatment, Proceedings of the IEEE 31st Annual Northeast Bioengineering Conference, pp. 170-171, 2005.|
|4||Behari, J, Mechanism of accelerated bone fracture healing, Proceedings of the 20th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, vol. 6, pp. 2928-2930, 1998.|
|5||Blokhius, TJ, et al., Evaluation of strength of healing fractures with dual energy x-ray absorptiometry, Clinical Orthopaedics and Related Research, vol. 380, pp. 260-268, 2000.|
|6||Chao, YS, et al., Biophysical stimulation of bone fracture repair, regeneration and remodeling, European Cells and Materials, vol. 6, pp. 72-85, 2003.|
|7||Fritton, SP, The in vivo mechanical loading history of bone, Proceedings of the First Joint Conference of the Engineering in Medicine and Biology Society and the Biomedical Engineering Society, vol. 1, p. 501, 1999.|
|8||McKinley, DW, Follow-up radiographs to detect callus formation after fractures, Archives of Family Medicine, vol. 9, pp. 373-374, 2000.|
|9||Singh, VR, et al., Early detection of fracture healing of a long bone for better mass health care, Proceedings of the 20th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, vol. 20, pp. 3.17-3.18, 1998.|
|10||Siu, WS, et al., pQCT bone strength index may serve as a better predictor than bone mineral density for long bone breaking strength, Journal of Bone and Mineral Metabolism, vol. 21, pp. 316-322, 2003.|
|11||Turner, CH, Mechanical loading effects on bone cells, Proceedings of the First Joint Conference of the Engineering in Medicine and Biology Society and the Biomedical Engineering Society, vol. 2, p. 1300, 1999.|
|12||Yang, GY, et al., Fabrication and characterization of microscale sensors for bone surface strain measurement, Proceedings of IEEE Sensors, vol. 3, pp. 1355-1358, 2004.|
|U.S. Classification||600/587, 606/70, 606/281, 606/76|
|International Classification||A61B5/103, A61B17/80|
|Cooperative Classification||A61B5/4504, A61B5/053, A61B17/80, A61B5/0031|
|European Classification||A61B17/80, A61B5/053, A61B5/00B9|